Cardiac cycle synchronized sampling of impedance signal

ABSTRACT

A cardiac rhythm management device for obtaining transthoracic impedance. The device comprises a sensor for obtaining a signal indicative of an action of a heart, an impedance measurement circuit adapted to measure transthoracic impedance and a processor for utilizing the signal indicative of the action of the heart to sample the transthoracic impedance at sampling intervals commenced by fiducial markers in the signal indicative of the action of the heart, where the sampling of the impedance signal removes the component of a stroke volume of the heart from the signal and thereby provides lung ventilation information.

RELATED APPLICATIONS

This application is a Continuation of Ser. No. 10/612,388, now U.S. Pat. No. 7,200,440, filed on Jul. 2, 2003, which is incorporated herein by reference.

TECHNICAL FIELD

This document relates generally to implantable devices, and, in particular, to a system and method for obtaining transthoracic impedance information.

BACKGROUND

Many systems implantable into a patient's thorax include a pulse generator and an arrangement of endocardial or intravascular leads (hereinafter referred to as “leads”). The pulse generator delivers electrical stimuli to tissue via the leads to provide a desired therapy. For example, implantable pacemakers deliver timed sequences of low energy electrical stimuli, called pace pulses, to the heart via an intravascular lead. By properly timing the delivery of pace pulses, the heart can be induced to contract in proper rhythm, greatly improving its pumping efficiency. Implantable defibrillators are devices capable of delivering higher energy electrical stimuli to the heart. A defibrillator is capable of delivering a high-energy electrical stimulus via leads that is sometimes referred to as a defibrillation countershock. The countershock interrupts a fibrillation, allowing the heart to reestablish a normal rhythm for efficient pumping of blood. These systems are able to sense cardiac signals and deliver therapy to the heart based on such signals.

The arrangement of the leads of such systems in the thorax region allows for other physiologic signals to be sensed. One type of physiologic signal is the transthoracic (i.e. across the chest) impedance of a patient with such a device. One approach to measure transthoracic impedance is described in Hartley et al., U.S. Pat. No. 6,076,015 “RATE ADAPTIVE CARDIAC RHYTHM MANAGEMENT DEVICE USING TRANSTHORACIC IMPEDANCE,” assigned to the assignee of the present application and which is incorporated herein by reference. The transthoracic impedance signal includes multiple components. A first component of the impedance varies with a patient's breathing and is useful in determining how fast (breathing rate) or how deeply (lung tidal volume) a patient is breathing. Information concerning a patient's breathing over a period of time is useful to an implantable pacemaker system as a metabolic indication that the patent's heart rate needs to be adjusted. However, the measurement of this respiratory component of the transthoracic impedance is complicated by other components of the impedance signal. For example, transthoracic impedance also varies with the volume of blood in a patient's heart and thus varies during a patient's heartbeat or cardiac cycle. This component is sometimes referred to as the cardiac stroke volume. This stroke volume component is close in frequency to the respiratory component. The closeness of the frequencies makes it difficult to separate the two components from each other. Previous solutions to the problem have used filtering circuitry to remove all but the breathing component of the transthoracic signal. However, because implantable systems are battery powered and are implanted for long periods of time, methods that perform a function with lower power consumption extending the battery life are valuable in such systems. Thus there is a need for a device and method to measure the respiratory component of the transthoracic impedance that has low power consumption.

SUMMARY

This document discusses a cardiac rhythm management device and method for obtaining impedance information from a thorax region of a patient. The device comprises a sensor for obtaining a signal indicative of an action of a heart, an impedance measurement circuit adapted to measure transthoracic impedance and a processor for utilizing the signal indicative of the action of the heart to sample the transthoracic impedance at sampling intervals commenced by fiducial markers in the signal indicative of the action of the heart, where the sampling of the impedance signal removes the component of a stroke volume of the heart from the signal and thereby providing lung ventilation information.

The method of measuring a transthoracic impedance comprises detecting intrinsic heart activity signals, applying a predetermined pulsed current stimulus across a thorax region of a patient in a predetermined time relationship to a fiducial marker, sampling a voltage across the thorax region when applying the predetermined pulsed current stimulus, and calculating an impedance from the measured voltage and the predetermined pulsed current stimulus.

This summary is intended to provide an overview of the subject matter of the present application. It is not intended to provide an exclusive or exhaustive explanation of the invention. The detailed description is included to provide further information about the subject matter of the preset patent application.

BRIEF DESCRIPTIONS OF THE DRAWINGS

In the drawings like numerals refer to like components throughout the several views.

FIG. 1 shows a block diagram of a cardiac rhythm management system that samples transthoracic impedance in a predetermined time relationship to a fiducial marker.

FIG. 2 illustrates an embodiment of the system implanted in a thorax region.

FIG. 3 shows a block diagram of a multi-lead embodiment of the system.

FIG. 4 illustrates a multi-lead embodiment of the system implanted in a thorax region.

FIG. 5 is a representation of a transthoracic impedance signal sampled in a predetermined time relationship to a fiducial marker.

FIG. 6 is an illustration of a filtered transthoracic impedance signal compared to an R-wave synchronized sampled impedance signal during deep and slow breathing.

FIG. 7 is an illustration of a filtered transthoracic impedance signal compared to an R-wave synchronized sampled impedance signal during fast and shallow breathing.

FIG. 8 is a flow chart illustrating a method of measuring transthoracic impedance.

FIG. 9 is a flow chart illustrating a method of monitoring lung ventilation.

DETAILED DESCRIPTION

In the following detailed description, reference is made to the accompanying drawings which form a part hereof, and in which is shown by way of illustration specific embodiments in which the invention may be practiced. It is to be understood that other embodiments may be utilized and structural changes may be made without departing from the scope of the present invention.

As discussed previously, the measurement of the respiratory component of the transthoracic impedance is complicated by the presence of the stroke volume component of the impedance signal. Because the stroke volume component is present due to the filling and emptying of the heart with blood, this component is synchronized to heartbeats. Implantable systems are able to sense intrinsic activity signals associated with heartbeats. The implantable systems are further able to generate fiducial markers in response to occurrences of such an activity signals. As an example, one of these activity signals is a QRS complex. A QRS complex is the activity signal associated with the process of the ventricular chambers depolarizing or contracting to empty the chambers of blood. In general, the volume of blood in the heart at an occurrence of an activity signal is fairly consistent from one occurrence of the signal to the next. Thus, the stroke volume component of the transthoracic impedance will also be fairly consistent at each occurrence of the signal. If the transthoracic impedance is sampled synchronously only when the implantable system generates a specific fiducial marker, the stroke volume component will be constant during the sampling and the respiratory signal is easily extracted from the transthoracic impedance signal. Examples of intrinsic heart activity signals sensed by implantable systems and useful for sampling include an onset of a P-wave, an onset of a QRS complex, an R-wave peak, or a T-wave peak.

FIG. 1 shows one embodiment of a system 100 for sampling the transthoracic impedance commenced at the occurrence of a fiducial marker. This embodiment of the system includes pulse generator 105 and endocardial lead 110. Lead 110 is shown coupled to pulse generator 105. Lead 110 is a multi-conductor lead and includes tip electrode 120 coupled to a first conductor and ring electrode 125 coupled to a second lead conductor. Pulse generator 105 includes a hermetically sealed outer housing 130. Outer housing 130 (sometimes referred to as the case or can) is comprised of a conducting material such as titanium, and is covered by an insulating material such as silicone rubber. A hole or window in the insulating material allows a third electrode 135 to be formed from the can 130 of pulse generator 105.

Pulse generator 105 also includes a header 140 for receiving the lead 110 and is formed from an insulating material such as molded plastic. Header 140 also includes a fourth electrode 145. Such a four-electrode system is described in Hauck et al., U.S. Pat. No. 5,284,136 “DUAL INDIFFERENT ELECTRODE PACEMAKER,” assigned to the assignee of the present application and which is incorporated herein by reference. Other embodiments of the system include a two or three electrode system. In the embodiment shown, lead 110 is implanted in the right ventricle of a heart 115. In this embodiment, the impedance sampling may begin, for example, at a fiducial marker indicating the onset of a QRS complex, at a fiducial marker indicating a peak of the R-wave, or at a fiducial marker indicating a peak of the T-wave.

FIG. 1 also illustrates portions of pulse generator 105. Therapy circuit 170 provides electrical pacing stimuli to the heart 115. Such pacing stimuli include providing bipolar pacing between tip electrode 120 and ring electrode 125 to initiate a contraction of the ventricles. Controller 165 adjusts the rate of the pacing stimuli delivered by the therapy circuit 170. Signal Processor 155 senses an intrinsic heart activity signal. When signal processor 155 senses the onset of an intrinsic heart activity signal, controller 165 initiates an impedance measurement. Exciter 150 delivers an electrical excitation signal, such as a pulsed current stimulus or any other suitable measurement stimulus, to heart 115. In one embodiment, exciter 150 delivers a predetermined current stimulus between ring electrode 125 and can electrode 135. In other embodiments exciter 150 delivers a current stimulus between any other suitable combinations of electrodes. Signal processor 155 senses the response to the excitation signal. In one embodiment, signal processor 155 senses the response between tip electrode 120 and header electrode 145. In other embodiments, signal processor 155 senses the response between any other suitable combinations of electrodes. Receiver 156 of the signal processor 155 receives a voltage through sampling element 175 in response to the onset of an intrinsic heart activity signal and the current stimulus. In the embodiment shown sampling element 175 is placed in series with header electrode 145 and the receiver 156. In another embodiment the sampling element is placed in series with the lead electrodes 120, 125 and the receiver 156. The signal processor 155 then measures the voltage by any method known in the art such as by an Analog to Digital converter. Transthoracic impedance is obtained from the predetermined current stimulus and the measured voltage. The transthoracic impedance may then be used to determine respiratory information.

FIG. 2 illustrates the system 100 implanted in the thorax region of a patient. It can be seen from the positioning of pulse generator 105 and lead electrodes 120 and 125 that the system 100 measures the impedance across a substantial portion of the patient's thorax. In one embodiment of the system 100, a time index is stored along with the impedance value obtained. The time index and impedance value are then used to derive a lung tidal volume. As discussed in the Hartley patent, lung tidal volume is obtained by taking the difference between the maximum and minimum impedance values stored for the patient's previous breath. A larger tidal volume value indicates a deeper breath for the patient than a smaller tidal volume value. In another embodiment, respiratory rate is derived from the impedance signal. One method to obtain respiratory rate would be to determine the time interval between maximum impedance values over a period of time and convert the data to breaths per minute. Based on information from the lung tidal volume and respiratory rate, controller 165 adjusts the rate of the delivery of therapy to the heart 115. A further embodiment of the system 100 is a combination of cardiac rhythm management and treatment for sleep apnea. In this embodiment, the system 100 determines if the respiratory activity falls below a predetermined level. If the respiratory activity falls below the predetermined level, the system provides therapy to treat the sleep apnea such as diaphragmatic pacing. An apparatus for diaphragmatic pacing to treat sleep apnea is described in Scheiner et al., U.S. Pat. No. 6,415,183 “A METHOD AND APPARATUS FOR DIAPHRAGMATIC PACING,” assigned to the assignee of the present application and which is incorporated herein by reference.

FIG. 3 shows an embodiment of the system 100 that uses multiple endocardial leads 100, 111. Leads 110, 111 are multi-conductor leads and include tip electrodes 120, 121 coupled to a first conductor and ring electrodes 125, 126 coupled to a second lead conductor within their respective lead. In the embodiment shown, lead 110 is implanted in the right ventricle of a heart 115 and lead 111 is implanted in the right atrium of the heart. If lead 111 is used to measure the impedance, the impedance sampling may begin, for example, at a fiducial marker indicating the onset of the P-wave rather than the QRS complex or the peak of an R-wave.

This embodiment of the system 100 further shows a pulse generator 105 that includes selector 180. Selector 180 is able to change the electrode combination providing the stimulus from a combination including ring electrode 125 to a combination including ring electrode 126. Selector 180 also changes the electrode combination measuring the stimulus response from a combination including tip electrode 120 to a combination including tip electrode 121. This ability to change the electrode combination is useful if, for example, measuring the sensed response using tip electrode 120 proves to be difficult due to signal noise, and use of another combination of electrodes provides a better measurement. It should be noted that other embodiments of the system 100 deliver the current stimulus or measure the response between any other suitable combinations of electrodes.

FIG. 4 illustrates a multiple lead embodiment of the system 100 implanted in the thorax region of a patient. It can be seen from the positioning of pulse generator 105 and lead electrodes 120, 121 and 125, 126 that the system 100 measures the impedance across a substantial portion of the patient's thorax. It can also be seen that selecting different combinations of electrodes will result in an impedance measurement taken across different vectors of the thorax. For example, using tip and ring electrodes 121, 126 and header and can electrodes 145, 135 will measure impedance across a vector originating from the atrium, while using tip and ring electrodes 120, 125 and can electrodes 145, 135 will measure impedance across a vector originating from the ventricle. Thus, it is beneficial for the system 100 to have flexibility in its measurement configuration to take full advantage of its positioning.

FIG. 5 is a graphical illustration 500 of sampling the transthoracic impedance synchronously to fiducial markers that indicate R-wave peaks. QRS complexes from heart activity are shown in graph 510. In graph 520, a transthoracic impedance signal obtained by sampling every 50 milliseconds is shown. The variation of the impedance signal with cardiac stroke volume can be seen. It can also be seen that the higher frequency stroke volume component is superimposed onto a lower frequency respiratory component. The downwardly pointing arrows shown in graph 520 correspond to the occurrence of R-waves in graph 510. Graph 530 shows the impedance signal obtained when the impedance is sampled synchronously to the R-waves. Graph 530 shows that the lower frequency respiratory signal is extracted from the higher frequency stroke volume component.

FIG. 6 is a graphical illustration 600 of sampling the transthoracic impedance during deep and slow breathing. Graph 610 shows the R-waves from heart activity. Graph 620 shows the transthoracic impedance signal obtained by sampling at a frequency high enough to obtain both the stroke volume and the respiratory component. Graph 630 shows the respiratory component obtained through sampling and filtering with a 4^(th)-order Elliptic Low Pass Filter with the filter pole at 0.2 Hertz(Hz). In implantable devices, such filters are generally implemented with active circuits. While these circuits can be designed to operate at low power, even low power circuits have an appreciable effect on battery life when the implanted period is on the order of five years. Graph 640 shows the respiratory component obtained with R-wave synchronous sampling. Graphs 630 and 640 show that similar results are obtained concerning phase, amplitude and frequency using the low pass filtering method and the R-wave sampling method. Thus, similar results for impedance measurements at slow and deep breathing can be attained while conserving the power required by an active low pass filtering circuit.

FIG. 7 is a graphical illustration 700 of sampling the transthoracic impedance during fast and shallow breathing. Graph 710 shows the R-waves of heart activity. Graph 720 shows the transthoracic impedance signal obtained by sampling at a frequency high enough to obtain both the stroke volume and the respiratory component. Graph 730 shows the respiratory component obtained with R-wave synchronous sampling. Graph 740 shows the respiratory component obtained from the high frequency sampling filtering with a 4^(th)-order Elliptic Low Pass Filter with the filter pole at 0.2 Hertz (Hz). Graph 750 shows the actual measured air volume passing through the lungs of the patient. A comparison of graphs 740 and 750 shows that in attempting to capture the transthoracic impedance during fast and shallow breathing, a 0.2 Hz pole can mask some of the impedance information as the frequency of the respiratory activity approaches the frequency of the stroke volume. Graph 730 shows that R-wave synchronous sampling has some advantage in reproducing amplitude information. This is because the sampling increases with the heart rate of the patient. Thus, somewhat improved results for impedance measurements at fast and shallow breathing can be attained while conserving the power required by an active low pass filtering circuit.

FIG. 8 is a flow chart illustrating a method 800 of measuring transthoracic impedance. At 810, a predetermined pulsed current stimulus is applied across a thorax region of a patient in synchrony with intrinsic heart activity signals. At 820, a voltage across the thorax region is sampled when applying the predetermined pulsed current stimulus. At 830, impedance is calculated from the measured voltage and the predetermined pulsed current stimulus.

FIG. 9 is a flow chart illustrating a method of monitoring lung ventilation. At 910, a predetermined pulsed current stimulus is applied across a thorax region of a patient in synchrony with intrinsic heart activity signals. At 920, a voltage across the thorax region is sampled when applying the predetermined current stimulus. At 930, impedance is calculated from the sampled voltage and the predetermined current stimulus. At 940, respiratory activity is determined from the calculated impedance.

Although specific examples have been illustrated and described herein, it will be appreciated by those of ordinary skill in the art that any arrangement calculated to achieve the same purpose could be substituted for the specific example shown. This application is intended to cover any adaptations or variations of the present invention. Therefore, it is intended that this invention be limited only by the claims and the equivalents shown. 

1. A cardiac management system comprising: an implantable device, including: a memory circuit; an intrinsic cardiac signal sensor; an impedance measurement circuit configured for generating a sampled transthoracic impedance signal; and a processor, coupled to the intrinsic cardiac signal sensor and the impedance measurement circuit, the processor configured to: initiate sampling of a transthoracic impedance signal substantially at an instance of a fiducial marker in a sensed intrinsic cardiac signal, the sampling to attenuate or remove a cardiac stroke component from the transthoracic impedance signal and to preserve a respiratory component of the transthoracic impedance signal; and measure a time interval between successive occurrences of the fiducial marker indicative of a cardiac cycle and to store a value in the memory circuit representative of the sampled measured transthoracic impedance in correspondence with an indication of the measured time interval; and determine lung information using the sampled measured transthoracic impedance in correspondence with an indication of the measured time interval.
 2. The system claim 1, wherein the fiducial marker includes an R-wave peak.
 3. The system of claim 1, wherein the processor is configured to determine ventilation information using the respiratory component of the transthoracic impedance signal.
 4. The system of claim 3, wherein the processor is configured to combine sampled values of transthoracic impedance signal to reconstruct a signal indicative of respiratory activity.
 5. The system of claim 1, including a memory communicatively coupled to the processor, and wherein the processor is configured to measure a time interval from a past occurrence of the fiducial marker to a present occurrence of the fiducial marker and to store a value in the memory representative of the measured impedance in association with the measured time interval.
 6. The system of claim 1, wherein the implantable device is configured for estimating lung tidal volume using the sampled measured transthoracic impedance in correspondence with an indication of the measured time interval.
 7. The system of claim 5, wherein the implantable device is configured for determining a respiratory rate using the stored value representative of the measured impedance.
 8. The system of claim 1, wherein the impedance measurement circuit includes: an exciter configured for delivering a pulsed current stimulus to at least two electrodes; a sampling circuit, coupled to the processor, configured to provide the sampled transthoracic impedance signal in response to instances of the fiducial marker; and at least one endocardial lead coupled to the implantable device and configured for placement in a plurality of locations in a thorax of a patient for delivering electrical energy thereto, wherein the endocardial lead includes at least a first implantable electrode.
 9. The system of claim 8, including a housing for the implantable device, an outer surface of the housing further comprising a second implantable electrode.
 10. The system of claim 8, including a header, coupled to the housing to receive the endocardial lead, and carrying a header electrode comprising a second implantable electrode.
 11. The system of claim 8, wherein the implantable device includes a plurality of endocardial leads and a selector, wherein the selector is configured for coupling the exciter and processor to a selected endocardial lead, wherein the exciter is coupled to the first electrode of the endocardial lead and the processor is coupled to a different electrode, such that selecting a different lead causes the exciter to apply the pulsed current stimulus as a different vector in a thorax.
 12. The system of claim 8, wherein the implantable device includes: an electrical stimuli delivery circuit, coupled to at least one electrode; and a controller, coupled to the therapy circuit for adjusting a rate of delivery of the electrical stimuli using the respiratory component of the transthoracic impedance signal.
 13. The system claim 1, wherein the fiducial marker includes an onset of a P-wave.
 14. The system claim 1, wherein the fiducial marker includes an onset of a QRS complex.
 15. The system claim 1, wherein the fiducial marker includes a T-wave peak.
 16. A method of measuring transthoracic impedance with an implantable medical device, the method comprising: sensing an intrinsic cardiac signal; generating a transthoracic impedance signal; sampling the transthoracic impedance signal substantially at an instance of a fiducial marker in the sensed intrinsic cardiac signal, wherein the sampling removes a cardiac stroke component from the transthoracic impedance signal and preserves a respiratory component of the transthoracic impedance signal; measuring a time interval between successive occurrences of the fiducial marker indicative of a cardiac cycle; storing a value representative of the sampled measured transthoracic impedance in correspondence with an indication of the measured time interval; and determining lung information using the sampled measured transthoracic impedance in correspondence with an indication of the measured time interval.
 17. The method of claim 16, wherein the fiducial marker includes an R-wave peak.
 18. The method of claim 16, wherein the fiducial marker includes an onset of a P-wave.
 19. The method of claim 16, wherein the fiducial marker includes an onset of a QRS complex.
 20. The method of claim 16, wherein the fiducial marker includes a T-wave peak.
 21. The method of claim 16, wherein sampling the transthoracic impedance signal includes: detecting fiducial markers in the sensed intrinsic cardiac signal; applying a pulsed current stimulus in a specified time relationship to an occurrence of a fiducial marker; sampling a voltage resulting from the pulsed current stimulus, such that a component of the voltage from a cardiac stroke volume is substantially constant; and calculating an impedance from the sampled voltage and the pulsed current stimulus.
 22. The method of claim 21, wherein the sampling a voltage includes changing the sampling rate according to a change in heart rate.
 23. The method of claim 21 including: providing respiratory activity information from the calculated impedance; and providing a therapy for stimulating breathing activity if the respiratory activity information indicates the respiratory activity falls below a specified level.
 24. The method of claim 16, wherein the method includes: storing data representing the transthoracic impedance; measuring a time interval from a first occurrence of the fiducial marker to a second occurrence of the fiducial marker; and storing the time interval in association with the data representing the transthoracic impedance.
 25. The method of claim 24, comprising estimating a lung tidal volume using the sampled measured transthoracic impedance in correspondence with an indication of the measured time interval.
 26. The method of claim 16, including: providing ventilation information using the respiratory component of the transthoracic impedance signal; and using the ventilation information for changing a therapy delivered in a system for treating cardiac arrhythmia. 